US20050099597A1 - Light adjustable multifocal lenses - Google Patents

Light adjustable multifocal lenses Download PDF

Info

Publication number
US20050099597A1
US20050099597A1 US10/915,948 US91594804A US2005099597A1 US 20050099597 A1 US20050099597 A1 US 20050099597A1 US 91594804 A US91594804 A US 91594804A US 2005099597 A1 US2005099597 A1 US 2005099597A1
Authority
US
United States
Prior art keywords
lens
portion
focal length
stimulus
multifocal
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US10/915,948
Inventor
Christian Sandstedt
Jagdish Jethmalani
Shiao Chang
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Calhoun Vision Inc
Original Assignee
Calhoun Vision Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority to US10/328,859 priority Critical patent/US20030151831A1/en
Priority to US49496903P priority
Application filed by Calhoun Vision Inc filed Critical Calhoun Vision Inc
Priority to US10/915,948 priority patent/US20050099597A1/en
Assigned to CALHOUN VISION reassignment CALHOUN VISION ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: JETHMALANI, JAGDISH M., CHANG, SHIAO H., SANDSTEDT, CHRISTIAN A.
Priority claimed from US11/083,794 external-priority patent/US7281795B2/en
Publication of US20050099597A1 publication Critical patent/US20050099597A1/en
Application status is Abandoned legal-status Critical

Links

Images

Classifications

    • GPHYSICS
    • G02OPTICS
    • G02CSPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
    • G02C7/00Optical parts
    • G02C7/02Lenses; Lens systems ; Methods of designing lenses
    • G02C7/06Lenses; Lens systems ; Methods of designing lenses bifocal; multifocal ; progressive
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/14Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
    • A61F2/16Intraocular lenses
    • A61F2/1613Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/14Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
    • A61F2/16Intraocular lenses
    • A61F2/1613Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus
    • A61F2/1616Pseudo-accommodative, e.g. multifocal or enabling monovision
    • A61F2/1618Multifocal lenses
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/14Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
    • A61F2/16Intraocular lenses
    • A61F2/1613Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus
    • A61F2/1624Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus having adjustable focus; power activated variable focus means, e.g. mechanically or electrically by the ciliary muscle or from the outside
    • A61F2/1627Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus having adjustable focus; power activated variable focus means, e.g. mechanically or electrically by the ciliary muscle or from the outside for changing index of refraction, e.g. by external means or by tilting
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/14Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
    • A61F2/16Intraocular lenses
    • A61F2/1613Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus
    • A61F2/1624Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus having adjustable focus; power activated variable focus means, e.g. mechanically or electrically by the ciliary muscle or from the outside
    • A61F2/1635Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus having adjustable focus; power activated variable focus means, e.g. mechanically or electrically by the ciliary muscle or from the outside for changing shape
    • GPHYSICS
    • G02OPTICS
    • G02CSPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
    • G02C2202/00Generic optical aspects applicable to one or more of the subgroups of G02C7/00
    • G02C2202/14Photorefractive lens material

Abstract

The invention relates to novel intraocular lenses. The lenses are capable of post-operative adjustment of their optical properties, including conversion from single focal lenses to multifocal lenses.

Description

    CROSS-REFERENCE TO RELATED APPLICATIONS
  • This application claims priority benefit of U.S. Provisional Patent Application No. 60/494,969 entitled “LIGHT ADJUSTABLE MULTIFOCAL LENSES,” filed Aug. 13, 2003, and is a continuation-in-part of U.S. patent application Ser. No. 10/328,859 entitled “LIGHT ADJUSTABLE MULTIFOCAL LENSES,” filed Dec. 24, 2002, the disclosures of which are hereby incorporated herein by reference.
  • TECHNICAL FIELD
  • The invention relates to optical elements, which can be modified post-manufacture such that different versions of the element will have different optical properties. In one embodiment, it relates to lenses, such as intraocular lenses, which can be converted into multifocal lenses post-fabrication.
  • BACKGROUND OF THE INVENTION
  • Accommodation, as it relates to the human visual system, refers to the ability of a person to use their unassisted ocular structure to view objects at both near (e.g. reading) and far (e.g. driving) distances. The mechanism whereby humans accommodate is by contraction and relaxation of the cilliary body which inserts into the capsular bag surrounding the natural lens. Under the application of cilliary stress, the human lens will undergo a shape change effectively altering the radius of curvature of the lens. This action produces a concomitant change in the power of the lens. However, as people grow older the ability for them to accommodate reduces dramatically. This condition is known as presbyopia and currently affects more than 90 million people in the US. The most widely believed theory to explain the loss of accommodation was put forth by Helmholtz and states that as the patient ages, the crystalline lens of the human eye becomes progressively stiffer prohibiting deformation under the applied action of the cilliary body.
  • People who can see objects at a distance without the need for spectacle correction, but have lost the ability to see objects up close are usually prescribed a pair of reading glasses or magnifiers. For those patients who have required previous spectacle correction due to preexisting defocus and/or astigmatism the patient is prescribed a pair of bifocals, trifocals, variable, or progressive focus lenses that allow the person to have both near and distance vision. Compounding this condition is the risk of cataract development as the patient ages. In fact, cataract extraction followed by intraocular lens (IOL) implantation is the most commonly performed surgery in patients over 65 years old (reference).
  • To effectively treat both presbyopia and cataracts the patient can be implanted with a multifocal IOL. The general concepts and designs of multifocal IOLs have been described before in the ophthalmic and patent literature. The simplest design for a multifocal IOL is commonly referred to as the “bull's eye” configuration and comprises a small, central add zone (1.5 mm to 2.5 mm in diameter) that provides near vision (“Intraocular Lenses in Cataract and Refractive Surgery,” D. T. Azar, et. al., W. B. Saunders Company (2001); “Intraocular Lenses: Basics and Clinical Applications,” R. L. Stamper, A Sugar, and D. J. Ripkin, American Academy of Ophthalmology (1993), both of which are hereby incorporated herein by reference). The power of the central add zone is typically between 3 to 4 diopters greater than the base power of the IOL, which translates to an effective add of 2.5 to 3.5 diopters for the entire ocular system. The portion of the lens outside the central add zone is referred to as the base power and is used for distance viewing. In theory, as the pupil constricts for near viewing, only that central add zone of the lens will have light from the image passing through it. However, under bright viewing conditions the pupil will also constrict leaving the patient 2 to 3 diopters myopic. This can be potentially problematic for a person who is driving in a direction with the sun shining straight at them, e.g. driving west around the time of sunset. To counteract this problem, an annular design with the central and peripheral portion of the lens designed for distance viewing and a paracentral ring (2.1 to 3.5 mm) for near vision. This design will maintain distance viewing even if the pupil constricts (Intraocular Lenses in Cataract and Refractive Surgery, D. T. Azar, et. al., W. B. Saunders Company (2001); “Intraocular Lenses: Basics and Clinical Applications,” R. L. Stamper, A Sugar, and D. J. Ripkin, American Academy of Ophthalmology (1993), which is hereby incorporated herein by reference). The most widely adopted multifocal IOL currently sold in the US is described in U.S. Pat. No. 5,225,858, which is hereby incorporated herein by reference. This IOL is known as the Array lens and comprises five concentric, aspheric annular zones. Each zone is a multifocal element and thus pupil size should play little or no role in determining final image quality.
  • However, as with standard intraocular lenses the power and focal zones of the lenses must be estimated prior to implantation. Errors in estimating the needed power as well as shifting of the lens post-operatively due to wound healing often results in less than optimal vision. The latter effect is particularly problematic for the case of the bull's eye lens if a transverse (perpendicular to the visual axis) shift of the IOL occurred during healing. This would effectively move the add part off the visual axis of the eye resulting in the lost of desired multifocality. The Array and paracentral IOL designs can partly overcome the dislocation problem during wound healing although any IOL movement longitudinally (the direction along the visual axis), preexisting astigmatism, or astigmatism induced by the surgical procedure can not be compensated using these multifocal IOL designs. This results in the patient having to choose between additional surgery to replace or reposition the lens or to use additional corrective lenses.
  • A need exists for an intraocular lens which can be adjusted post-operatively in vivo to form a multifocal intraocular lens. This type of lens can be designed in-vivo to correct to an initial emmetropic (light from infinity forming a perfect focus on the retina) state and then the multifocality may be added during a second treatment. Such a lens would remove some of the guess work involved in presurgical power selection, overcome the wound healing response inherent to IOL implantation, allow the size of the add or subtract zone(s) to be customized to correspond to the patient's magnitude and characteristics of dilation under different illumination conditions, and allow the corrected zones to be placed along the patient's visual axis.
  • BRIEF SUMMARY OF THE INVENTION
  • Novel optical elements are provided whose properties can be adjusted post-manufacture to produce an optical element having different properties. Specifically, the invention relates to an intraocular lens that can be transformed into a multifocal lens after the lens has been implanted in the eye. In this manner, the intraocular and/or focal zones of the lens can be more precisely adjusted after the lens has been subjected to any post-operative migration, and can be based on input from the patient and standard refraction techniques rather than preoperative estimation.
  • The alteration of the optical element is accomplished through the use of a modifying composition (“MC”) dispersed throughout the element. The MC is capable of polymerization when exposed to an external stimulus such as heat or light. The stimulus can be directed to one or more regions of the element causing polymerization of the MC only in the exposed regions. The polymerization of the MC causes changes in the optical properties of the element with exposed regions.
  • Upon polymerization, several changes occur within the optical element. The first change is the formation of a second polymer network comprising polymerized MC. The formation of this polymer network can cause changes in the optical properties of the element, namely the refractive index. In addition, when the MC polymerizes, a difference in the chemical potential between the polymerized and unpolymerized region is induced. This in turn causes the unpolymerized MC to diffuse within the element, thermodynamic equilibrium of the optical element is reestablished. If the optical element possesses sufficient elasticity, this migration of MC can cause swelling of the element in the area exposed to the stimulus. This, in turn, changes the shape of the element, causing changes in the optical properties. Depending upon the nature of the optical element, the MC incorporated into the element, the duration, and the spatial intensity profile of the stimulus either or both of these two changes can occur.
  • One key aspect of the present invention is that the optical elements are self-contained in that once fabricated, no material is either added or removed from the lens to obtain the desired optical properties.
  • It has been found that by exposing different regions of the optical element to varying degrees or in a predetermined pattern of external stimulus, it is possible to vary the optical properties of the element in different regions. For example, it is possible through the use of various patterns, to create a central zone with one set of optical properties, surrounded by concentric rings of differing optical properties. In this way, a multifocal lens can be created. In another embodiment, customized bifocal, multifocal, etc. patterns can be written on the lens in one treatment followed by a second treatment to lock-in the unreacted modifying composition present throughout the entire lens. Alternately, multiple treatments of customized patterns can be written on the lens to provide patients with vision without the need for spectacles.
  • The foregoing has outlined rather broadly the features and technical advantages of the present invention in order that the detailed description of the invention that follows may be better understood. Additional features and advantages of the invention will be described hereinafter which form the subject of the claims of the invention. It should be appreciated by those skilled in the art that the conception and specific embodiment disclosed may be readily utilized as a basis for modifying or designing other structures for carrying out the same purposes of the present invention. It should also be realized by those skilled in the art that such equivalent constructions do not depart from the spirit and scope of the invention as set forth in the appended claims. The novel features which are believed to be characteristic of the invention, both as to its organization and method of operation, together with further objects and advantages will be better understood from the following description when considered in connection with the accompanying figures. It is to be expressly understood, however, that each of the figures is provided for the purpose of illustration and description only and is not intended as a definition of the limits of the present invention.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • For a more complete understanding of the present invention, reference is now made to the following descriptions taken in conjunction with the accompanying drawing, in which:
  • FIGS. 1A and 1B depict a cross-section of an intraocular lens and a micrograph, according to an embodiment of the invention.
  • FIGS. 2A and 2B depict a cross-section of a multifocal intraocular lens and a micrograph, according to an embodiment of the invention.
  • FIGS. 3A through 3C depict interference fringes for a lens, according to an embodiment of the invention.
  • FIGS. 4A through 4C depict an example of reversible multifocality for a lens, according to an embodiment of the invention.
  • FIG. 5 is an example of a lens made according to embodiments of the invention.
  • FIGS. 6A through 6F depict a top-down view and a side view of an example of a multifocal lens according to embodiments of the invention.
  • FIGS. 7A through 7F depict a top-down view and a side view of an example of a multifocal lens according to embodiments of the invention.
  • FIG. 8 depicts a top-down view of an example of a multifocal lens according to embodiments of the invention.
  • FIG. 9 depicts a side view of an example of a multifocal lens according to embodiments of the invention.
  • FIGS. 10A-10D depict a series of interference patterns of a lens according to embodiments of the invention.
  • DETAILED DESCRIPTION OF THE INVENTION
  • The optical elements of the present invention are capable of post-fabrication alteration of optical properties. The elements are self-contained and do not require the addition or removal of materials to change the optical properties. Instead, the optical properties are altered by exposing a portion or portions of the optical element to an external stimulus which induces polymerization of a MC within the element. The polymerization of the MC, in turn, causes the change in optical properties.
  • The optical element of the invention has dispersed within it a MC. This MC is capable of diffusion within the element; can be readily polymerized by exposure to a suitable external stimulus; and is compatible with the materials used to make the optical element.
  • The optical element is typically made of a first polymer matrix. Illustrative examples of a suitable first polymer matrix include: polyacrylates such as polyalkyl acrylates and polyhydroxyalkyl acrylates; polymethacrylates such as polymethyl methacrylate (“PMMA”), polyhydroxyethyl methacrylate (“PHEMA”), and polyhydroxypropyl methacrylate (“HPMA”); polyvinyls such as polystyrene and polyvinylpyrrolidone (“PNVP”); polysiloxanes such as polydimethylsiloxane; polyphosphazenes, and copolymers of thereof. U.S. Pat. No. 4,260,725 and patents and references cited therein (which are all incorporated herein by reference) provide more specific examples of suitable polymers that may be used to form the first polymer matrix.
  • In preferred embodiments, where flexibility is desired, the first polymer matrix generally possesses a relatively low glass transition temperature (“Tg”) such that the resulting IOL tends to exhibit fluid-like and/or elastomeric behavior, and is typically formed by cross-linking one or more polymeric starting materials wherein each polymeric starting material includes at least one cross-linkable group. In the case of an intraocular lens, the Tg should be less than 25° C. This allows the lens to be folded, facilitating implantation. In cases where rigidity is desired, the Tg should generally be greater than 25° C.
  • Illustrative examples of suitable cross-linkable groups include but are not limited to hydride, acetoxy, alkoxy, amino, anhydride, aryloxy, carboxy, enoxy, epoxy, halide, isocyano, olefinic, and oxine. In more preferred embodiments, such polymeric starting material includes terminal monomers (also referred to as endcaps) that are either the same or different from the one or more monomers that comprise the polymeric starting material but include at least one cross-linkable group. In other words, the terminal monomers begin and end the polymeric starting material and include at least one cross-linkable group as part of its structure. Although it is not necessary for the practice of the present invention, the mechanism for cross-linking the polymeric starting material preferably is different than the mechanism for the stimulus-induced polymerization of the components that comprise the refraction modulating composition. For example, if the refraction modulating composition is polymerized by photoinduced polymerization, then it is preferred that the polymeric starting materials have cross-linkable groups that are polymerized by any mechanism other than photoinduced polymerization.
  • An especially preferred class of polymeric starting materials for the formation of the first polymer matrix is polysiloxanes (also known as “silicones”) endcapped with a terminal monomer which includes a cross-linkable group selected from the group consisting of acetoxy, amino, alkoxy, halide, hydroxy, and mercapto. Because silicone IOLs tend to be flexible and foldable, generally smaller incisions may be used during the IOL implantation procedure. An example of an especially preferred polymeric starting materials are vinyl endcapped dimethylsiloxane diphenylsiloxane copolymer, silicone resin, and silicone hydride crosslinker that are crosslinked via an addition polymerization by platinum catalyst to form the silicone matrix. Other such examples may be found in U.S. Pat. No. 5,236,970, U.S. Pat. No. 5,376,694, U.S. Pat. No. 5,278,258, U.S. Pat. No. 5,444,106, and others similar to the described formulations, which are hereby incorporated herein by reference.
  • The MC that is used in fabricating IOLs is as described above except that it has the additional requirement of biocompatibility. The MC is capable of stimulus-induced polymerization and may be a single component or multiple components so long as: (i) it is compatible with the formation of the first polymer matrix; (ii) it remains capable of stimulus-induced polymerization after the formation of the first polymer matrix; and (iii) it is freely diffusible within the first polymer matrix. In general, the same type of monomers that are used to form the first polymer matrix may be used as components of the refraction modulating composition. However, because of the requirement that the MC monomers must be diffusible within the first polymer matrix, the MC monomers generally tend to be smaller (i.e., have lower molecular weights) than the first polymer matrix. In addition to the one or more monomers, the MC may include other components such as initiators and sensitizers that facilitate the formation of the second polymer network.
  • In preferred embodiments, the stimulus-induced polymerization is photopolymerization. In other words, the one or more monomers that comprise the refraction modulating composition each preferably includes at least one group that is capable of photopolymerization. Illustrative examples of such photopolymerizable groups include but are not limited to acrylate, allyloxy, cinnamoyl, methacrylate, stibenyl, and vinyl. In more preferred embodiments, the refraction modulating composition includes a photoinitiator (any compound used to generate free radicals) either alone or in the presence of a sensitizer. Examples of suitable photoinitiators include acetophenones (e.g., substituted haloacetophenones, and diethoxyacetophenone); 2,4-dichloromethyl-1,3,5-trazines; benzoin methyl ether; and o-benzoyl oximino ketone. Examples of suitable sensitizers include p-(dialkyiamino)aryl aldehyde; N-alkylindolylidene; and bis[p-(dialkylamino)benzylidene] ketone.
  • Because of the preference for flexible and foldable IOLs, an especially preferred class of MC monomers is polysiloxanes endcapped with a terminal siloxane moiety that includes a photopolymerizable group. An illustrative representation of such a monomer is:
    X—Y—X1
    wherein Y is a siloxane which may be a monomer, a homopolymer or a copolymer formed from any number of siloxane units, and X and X1 may be the same or different and are each independently a terminal siloxane moiety that includes a photopolymerizable group. An illustrative example of Y includes:
    Figure US20050099597A1-20050512-C00001

    wherein: m and n are independently each an integer and
      • R1, R2, R3, and R4 are independently each hydrogen, alkyl (primary, secondary, tertiary, cyclo), aryl, or heteroaryl. In preferred embodiments, R1, R2, R3, and R4 are C1-C10 alkyl or phenyl. Because MC monomers with a relatively high aryl content have been found to produce larger changes in the refractive index of the inventive lens, it is generally preferred that at least one of R1, R2, R3, and R4 is an aryl, particularly phenyl. In more preferred embodiments, R1, R2, and R3 are the same and are methyl, ethyl or propyl and R4 is phenyl.
  • Illustrative examples of X and X1 (or X1 and X depending on how the MC polymer is depicted) are:
    Figure US20050099597A1-20050512-C00002

    respectively wherein:
      • R5 and R6 are independently each hydrogen, alkyl, aryl, or heteroaryl; and
      • Z is a photopolymerizable group.
  • In preferred embodiments R5 and R6 are independently each C1-C10 alkyl or phenyl and Z is a photopolymerizable group that includes a moiety selected from the group consisting of acrylate, allyloxy, cinnamoyl, methacrylate, stibenyl, and vinyl. In more preferred embodiments, R5 and R6 are methyl, ethyl, or propyl and Z is a photopolymerizable group that includes an acrylate or methacrylate moiety.
  • In especially preferred embodiments, a MC monomer is of the following formula:
    Figure US20050099597A1-20050512-C00003

    wherein X and X1 are the same as R1, R2, R3, and R4 areas defined previously. Illustrative examples of such MC monomers include dimethylsiloxane-diphenylsiloxane copolymer endcapped with a vinyi dimethylsilane group; dimethylsiloxane-methylphenylsiloxane copolymer endcapped with a methacryloxypropyl dimethylsilane group; and dimethylsiloxane endcapped with a methacryloxypropyldimethylsilane group. Although any suitable method may be used, a ring-opening reaction of one or more cyclic siloxanes in the presence of triflic acid has been found to be a particularly efficient method of making one class of inventive MC monomers. Briefly, the method comprises contacting a cyclic siloxane with a compound of the formula:
    Figure US20050099597A1-20050512-C00004

    in the presence of triflic acid wherein R5 and R6, and Z are as defined previously. The cyclic siloxane may be a cyclic siloxane monomer, momopolymer, or copolymer. Alternatively, more than one cyclic siloxane may be used. For example, a cyclic dimethylsiloxane tetrameter and a cyclic methyl-phenylsiloxane trimer are contacted with bis-methacryloxypropyltetramethyldisiloxane in the presence of triflic acid to form a dimethyl-siloxane methyl-phenylsiloxane copolymer that is endcapped with a methacryloxylpropyl-dimethylsilane group, an especially preferred MC monomer.
  • In addition to the silicone-based MCs described above, acrylate-based MC can also be used in the practice of the invention. The acrylate-based macromers of the invention have the general structure:
    X-An-Q-An-X1
    or
    X-An-A1 m-Q-A1 m-An-X1
    wherein Q is an acrylate moiety capable of acting as an initiator for Atom Transfer Radical Polymerization (“ATRP”), A and A1 have the general structure:
    Figure US20050099597A1-20050512-C00005

    wherein R1 is selected from the group comprising alkyls, halogenated alkyls, aryls and halogenated aryls and X and X1 are groups containing photopolymerizable moieties and m and n are integers.
  • In one embodiment the acrylate based MC has the formula:
    Figure US20050099597A1-20050512-C00006
  • wherein R2 is selected from the group comprising alkyls and halogenated alkyls R3 and R4 are different and are selected from the group consisting of alkyls, halogenated alkyls, aryls and halogenated aryls.
  • When the optical element is formed, it is then positioned in the area where it is to be used. For an intraocular lens, this means implantation into the eye using known procedures. Once the element is in place and is allowed to adjust to its environment, it is then possible to modify the optical properties of the element through exposure to an external stimulus.
  • The nature of the external stimulus can vary but it must be capable of reducing polymerization of the MC without adversely affecting the properties of the optical element. Typical external stimuli that can be used in practice of the invention include heat and light, with light preferred. In the case of intraocular lenses, ultraviolet or infrared radiation is preferred with ultraviolet light most preferred.
  • When the element is exposed to the external stimulus, the MC polymerization forms a second polymer matrix, interspersed with the first polymer matrix. When the polymerization is localized or when only a portion of the MC is polymerized, there is a difference in the chemical potential between the reacted and unreacted regions of the lens. The MC then migrates within the element to reestablish the thermodynamic equilibrium within the optical element.
  • The formation of the second polymer matrix and the re-distribution of the MC can each affect the optical properties of the element. For example, the formation of the second polymer matrix can cause changes in the refractive index of the element. The migration of the modifying compound can alter the overall shape of the element, further affecting the optical properties by changing the radii of curvatures of the optical element.
  • It is possible to localize the exposure of the optical element to the external stimulus in such a manner to create zones within the element with different optical properties. In one embodiment, it is possible to create an intraocular lens that can be transferred into a multifocal lens after implantation. This is accomplished by exposing the lens to different amounts of external stimulus to create zone(s) having different optical properties.
  • In the case of a multifocal intraocular lens, various methods can be used to create the lenses. In its simplest form, it can be of the bull's eye configuration comprising an add or subtract zone in the central 1 to 3 mm zone of the lens and the resultant lens base power outside this zone. The lenses can be divided into separate zones, alternating zones or overlapping zones. For example, separate zones would include outer and inner zones. A Fresnel lens is an example of alternating zones.
  • Overlapping zones are particularly useful in diffractive optical elements such as holograms, binary optic, kinoforms and holographic optical elements.
  • In the case of an intraocular lens, it is possible to form a lens, implant it, and then form different zones or regions in the lens having different optical properties. By exposing different areas of the lens to different magnitudes and spatial profiles of external stimuli, different optical zones can be created. For example, the lens body can be divided into central zone, inner and outer annular near zones, and annular far zones. In this embodiment, the central zone is circular and the peripheries of the annular zones are circular. The annular zones circumscribe the central zone and the zones are contiguous. The zones are concentric and coaxial with the lens body.
  • The zones are used in describing the vision correction power of the lens, and they are arbitrarily defined. Thus, the peripheries of the zones and the numbers of zones may be selected as desired.
  • The following examples are offered by way of example and are not intended to limit the scope of the invention in any manner.
  • EXAMPLE 1
  • A 6 mm diameter intraocular lens containing a silicone-based MC was prepared using standard molding techniques known to those skilled in the art. The lens had a first polymer matrix prepared from a silicone hydride crosslinked vinyl endcapped diphenylsiloxane dimethylsiloxane. The first polymer matrix comprised about 70 weight % of the lens. The lens also comprised about 30 weight % of a MC (methacrylate endcapped polydimethylsiloxane), 1 weight % (based on MC) of a photoinitiator (benzoin-tetrasiloxane-benzoin), and 0.04 weight % (based on MC) UV absorber. The lens had an initial nominal power of 30 diopters. The center of the lens was then irradiated with 365 nm light using an intensity pattern represented by the equation: I = I 0 - ( r - r c ) 2 2 σ 2 ( 1 )
    and an average intensity of 4.12 mW/cm2 for 60 seconds. Three hours post-exposure, the lens had a +3.25 D change over the central 2.5 mm region of the lens, which is shown in FIG. 1A. The interference fringes were taken at the preirradiation best focus position. The affected zone is easily observed in the central portion of the light adjustable lens (LAL) and is distinguished by the approximately 6 fringes (in double pass) of defocus in the central portion of the IOL. FIG. 1B depicts a micrograph of FIG. 1A.
  • In another embodiment, the first polymer matrix comprised about 75 weight % of the lens. The lens also comprised about 25 weight % of a MC (methacrylate endcapped methylphenylsiloxane dimethylsiloxane), 0.83 weight % (based on MC) of a photoinitiator (benzoin-L4-benzoin), and 0.04 weight % (based on MC) UV absorber. The lens had an initial nominal power of +20.0 diopters. The lens was then irradiated with 365 nm (±5 nm) light using a spatial intensity profile described by the following equation: I = I 0 ( 0.65 r 2 r max 2 + 0.35 ) ( 2 )
  • The IOL was irradiated with an average intensity of 6 mW/cm2 using three, 15 second exposures separated by 5 seconds. FIGS. 2A and 2B display the interference fringes (in double pass) of the lens before irradiation and 24 hours post irradiation. FIG. 2A depicts the Fizeau interference fringe (in double pass) of a +20.0 D LAL at best focus preirradiation, the same LAL 24 hours after irradiation at the original best focus position. FIG. 2B depicts the LAL of FIGS. 2A. The most striking feature between the two interferograms is the presence of a 3 mm reaction zone in the central portion of the lens, which is from the introduction of defocus. The change corresponds to a −0.70 diopters change in this central region.
  • These two examples illustrate that we can both add and subtract power from the central portion of the lens as well as control the effected zone size.
  • These two multifocal designs are similar to the bull's eye design described above. The difference between our design and those already presented in the literature and other patents is that we have the ability to affect the change post-operatively after wound healing has occurred, customize the zone size to fit the patient's dilation conditions, add or subtract different amounts of power depending upon the recommendation of the patient or physician, and center the zone along the patient's visual axis once post-operative healing has finished.
  • EXAMPLE 2
  • One of the unique aspects of the above described technology is that we have the ability to first change the power of the IOL over the majority of its aperture and then reirradiate the lens over a small zone (0 to 3 mm) to create a bifocal lens as described in example 1. This embodiment has the advantages of first implanting the light adjustable lens in the patient, waiting the required healing time to let the eye refractively stabilize (typically two to four weeks), measuring the refraction of the patient to determine the necessary correction, if any, to bring the patient to emmetropia, irradiating the lens to change the power of the lens over the majority of the aperture, and then reirradiating a smaller zone in the lens (1.5-3 mm) along the patient's visual axis to provide the necessary multifocality for near and distance viewing.
  • As an example of this, a +20.0 D LAL was molded comprising 75 wt % of silicone matrix, 25 wt % of MC, 0.83 wt % PI, and 0.04 wt % UV absorber. The lens was initially irradiated using an average intensity of 10 mW/cm2 using a spatial profile described by equation 2 above. The lens was dosed using seven 15 second exposures (5 seconds between each exposure). This treatment induced −1.32 diopters of change in the lens over a 5.5 region of the aperture. Twenty four hours post-irradiation, the lens was reirradiated in the central portion of the lens using the intensity profile represented by equation 1. The beam size was reduced to 3 mm in diameter, the average intensity of light was 6 mW/cm2 and the dose was given in three 30 second doses. Twenty-four hours post irradiation; we observed a change of 1.94 diopters in this central region.
  • FIG. 3A depicts Fizeau interference fringes (in double pass) of a +20.0 D LAL at best focus preirradiation. FIG. 3B depicts the approximately 8 fringes (in double pass) of defocus introduced by the initial irradiation. This procedure introduced −1.32 diopters of change from the initial base power of +20.0 diopters. FIG. 3C depicts the same LAL at the best focus position 24 hours after the initial irradiation. Note the presence of a new focus zone in the central part of the lens. This zone corresponds to +1.94 diopters of change.
  • EXAMPLE 3
  • In the past, the clinical use of bifocal or multifocal IOLs have met with some resistance by patients due to the loss of contrast sensitivity and glare that are inherent to this type of lens' designs. In the past, the only way for a physician to reverse the undesired affects of a previously implanted multifocal or bifocal IOL was to explant the IOL and reinsert it with a standard monofocal IOL. However, the light adjustable lens technology described in this disclosure and previous Calhoun Vision published works provides a means to reverse the multifocal properties of the LAL, effectively returning it to its monofocal condition. Such ability would have the oblivious advantage of reversal without surgical explantation.
  • As an example of this process, a +20.0 D LAL was molded comprising 75 wt % of silicone matrix, 25 wt % of MC, 0.83 wt % PI, and 0.04 wt % UV absorber. The preirradiation Fizeau interference fringes are shown in FIG. 4A. This LAL was then irradiated using two successive, 30-second exposures of 6 mW/cm2. The spatial intensity profile of this initial irradiation is described by equation 2. As displayed in FIG. 4B, −0.5 D of power were removed from the central optical zone of this lens. Twenty-four hours after this initial irradiation, the LAL was irradiated again using two successive, 30-second exposures of 3 mW/cm2. The second irradiation effectively overlaid on top of the initial dose. The spatial intensity profile of this second irradiation is described by equation 1. This second irradiation added +0.5 D of power to the initially irradiated region, effectively removing the initial subtraction of power from the LAL and showing an example of multifocal reversibility in the Calhoun Vision LAL.
  • FIGS. 4A, 4B and 4C depict an example of reversible multifocality. FIG. 4A depicts preirradiation Fizeau interference fringes of a +20.0 diopters LAL at best focus. FIG. 4B Fizeau interference fringes at the preirradiation best focus 24 hours post initial irradiation. Note that −0.5 diopters of spherical power have been subtracted from the central portion of the LAL as noted by the fringes of defocus in the central portion of the LAL. FIG. 4C depicts Fizeau interference fringes at the preirradiation best focus position two hours post the second irradiation showing the removal of the defocus fringes. This indicates that the LAL has been effectively brought back to its preirradiation power.
  • FIG. 5 depicts an example of a lens 500 formed according to embodiments of the invention. The lens includes a plurality of different focal zones, 501, 502, 503, 504, 505, and 506. Note that the number of zones is by way of example only, as more or fewer zones could be used. For example, there may be five concentric annular zones. The different zones are preferably concentric about a central zone 501. The different zones may have different radial widths, e.g. zone 504 has a smaller radial width than zone 503. Similarly, the different zones may have different areas, e.g. the area of zone 501 is smaller than the area of zone 503. Alternatively, some or all of the zones may have the same radial width and/or area as other zones. Each zone may have a different focal length or diopter than each of the other zones, e.g. zone 502 may be +1.0 diopter with respect to zone 501, and zone 503 may be +1.0 diopter with respect to zone 502, etc. Alternatively, some zones may have the same power, while other zones have different powers. For example, zones 501, 503, and 505 may have the same power, while zones 502, 504, and 506 may be +1.0 diopter with respect to zone 501. As another example, zones 501, 503, and 505 may have the same power, while zone 502 may be +1.0 diopter with respect to zone 501, zone 504 may be +1.0 diopter with respect to zone 502, and zone 506 may be +1.0 diopter with respect to zone 504. Note that some zones may have a negative diopter with respect to other zones. Further note that the different zones may correct for near vision, while other zones correct for far vision. The different zones may be in a pattern other than a “bulls-eye” patterns, e.g. a cylindrical pattern, which would be used to correct astigmatism. Any pattern zones may be formed into the lens. Lens 501 may be a eyeglass lens, a lens used in an optical system, or an intra-ocular lens. Note that a lens is used by way of example only, as other optical elements could be used. Further note that each zone may be spherical or aspherical.
  • FIGS. 6A and 6B depict a top-down view and a side view of an example of a multifocal lens 60 according to embodiments of the invention. Lens 60 includes region 61 that provides a user with near vision and region 62 provides a user with far vision.
  • FIGS. 6C-6F depict an example of a method of forming the lens of FIGS. 6A and 6B. The lens 60 comprises a photosensitive macromer 63 in a matrix 64. In FIG. 6A, the central zone of the lens 60 is selectively irradiated by radiation 65, e.g. ultraviolet light or near ultraviolet light (365 nanometers). The radiation causes the macromers 63 to from an interpenetrating network within the target area (the central zone), in other words the macromers 63 form polymerized macromers 66, in FIG. 6D. The formation of the polymerized macromers 66 produces a change in the chemical potential between the irradiated and unirradiated regions of the lens. To reestablish thermodynamic equilibrium, macromers 63 from the unirradiation portion 62 of the lens will diffuse into the irradiated portion, which produces a swelling in the irradiation portion 61, as shown in FIG. 6E. The swelling, in turn, changes the curvature of the lens.
  • By controlling the irradiation dosage (e.g. beam location, beam intensity), spatial intensity profile, and the target area, physical changes in the radius of curvature of the lens surface are achieved, thus modifying the refractive power of the lens. The characteristics of the lens may be modified to change the power of the lens, the spherical nature of the lens, the aspherical nature of the lens, reduce or eliminate astigmatic error, or correct other higher order aberrations. The application of the radiation 65 may be repeated until a desired amount of change has occurred. The radiation doses may be varied, e.g. one application corrects for astigmatism, while another application may provide the central add. Alternatively, the radiation may be controlled such that a single dose induces all desired effects.
  • After the lens has the desired optical characteristics, the lens is locked-in, as shown in FIG. 6E. During lock-in, the surface of the lens is irradiated by radiation 67 to polymerize most of the remaining unreacted macromer 63. This prevents any subsequent substantial change in lens characteristics from macromer diffusion. The completed lens is shown in FIG. 6F with the permanent change power and/or other characteristic(s).
  • Note that the it is desirable to irradiate the entire surface of the lens during lock-in, however, there may be some portions of the lens surface that cannot be irradiated because of its placement an optical system. For example, an interocular lens has been implanted into the eye of an animal (e.g. a human, rabbit, etc.), some portion(s) of the lens may be blocked by a feature(s) of the animal.
  • Note that prior to lock-in, if the change has become undesirable to the patient, the process may be reversed, so as to remove the change. The reversal would be done by irradiating the lens with a complementary pattern to that which was used to provide the change. This would cause diffusion of the macromer to peripheral portion of the lens and would compensate for the initial change, e.g. central add 61.
  • FIGS. 6A-6F depict a lens that has a central add, e.g. wherein the central zone has more diopters in power as compared with the surrounding area. A similar process can be used to produce a central subtract, e.g. by irradiating the outer periphery (not the central zone), which would cause a swelling of the outer periphery (and thus a dip or concave curvature in the central zone) and result in a decrease in the lens power of the lens.
  • In conditions of bright ambient light, e.g. driving a car into the sun, the pupil of the eye may close such that the far zone 62 of lens 60 is entirely blocked, leaving the user with only near vision. In such a case a lens such as lens 70 of FIGS. 7A and 7B may be preferable. FIGS. 7A and 7B depict a top-down view and a side view of an example of a multifocal lens 70 according to embodiments of the invention. Lens 70 includes regions 71 and 73 that provides a user with far vision, and while annulus region 72 provides a user with near vision.
  • FIGS. 7C-7F depict an example of a method of forming the lens of FIGS. 7A and 7B. The lens 70 comprises a photosensitive macromer 73 in a matrix 74. In FIG. 7A, an annular zone 72 that surrounds the central zone 71 of the lens 70 is selectively irradiated by radiation 75, e.g. ultraviolet light or near ultraviolet light (365 nanometers). The radiation causes the macromers 73 to from an interpenetrating network within the target area (the annular zone), in other words the macromers 73 form polymerized macromers 76, in FIG. 7D. The formation of the polymerized macromers 76 produces a change in the chemical potential between the irradiated and unirradiated regions of the lens. To re-establish thermodynamic equilibrium, macromers 73 from the unirradiation portion 71 of the lens will diffuse into the irradiated portion, which produces a swelling in the irradiation portion 72, as shown in FIG. 7E. The swelling, in turn, changes the curvature of the lens.
  • By controlling the irradiation dosage (e.g. beam location, beam intensity), spatial intensity profile, and the target area, physical changes in the radius of curvature of the lens surface are achieved, thus modifying the refractive power of the lens. The characteristics of the lens may be modified to change the power of the lens, the spherical nature of the lens, the aspherical nature of the lens, reduce or eliminate astigmatic error, or correct other higher order aberrations. The application of the radiation 75 may be repeated until a desired amount of change has occurred. The radiation doses may be varied, e.g. one application corrects for astigmatism, while another application may provide the annular add. Alternatively, the radiation may be controlled such that a single dose induces all desired effects.
  • After the lens has the desired optical characteristics, the lens is locked-in, as shown in FIG. 7E. During lock-in, the surface of the lens is irradiated by radiation 77 to polymerize most of the remaining unreacted macromer 73. This prevents any subsequent substantial change in lens characteristics from macromer diffusion. The completed lens is shown in FIG. 7F with the permanent change power and/or other characteristic(s).
  • Note that the it is desirable to irradiate the entire surface of the lens during lock-in, however, there may be some portions of the lens surface that cannot be irradiated because of its placement an optical system. For example, an interocular lens has been implanted into the eye of an animal (e.g. a human, rabbit, etc.), some portion(s) of the lens may be blocked by a feature(s) of the animal.
  • Note that prior to lock-in, if the change has become undesirable to the patient, the process may be reversed, so as to remove the change. The reversal would be done by irradiating the lens with a complementary pattern to that which was used to provide the change. This would cause diffusion of the macromer to peripheral portion of the lens and would compensate for the initial change, e.g. annular add 72.
  • FIGS. 7A-7F depict a lens that has an annular add, e.g. wherein the annular zone has more diopters in power as compared with the surrounding area and the central zone. A similar process can be used to produce an annular subtract, e.g. by irradiating the outer periphery and the central zone (not the annular zone), which would cause a swelling of the outer periphery and the central zone (and thus a dip or concave curvature in the annular zone) and result in a decrease in the lens power of the lens.
  • As discussed above, after implantation of an IOL, the lens may shift due to the healing of the patient. The shift may be a lateral shift in a direction that is orthogonal to the optical axis. In such a case, the base power may be adjusted and/or the multifocal power may be added after healing to compensate for the shift. FIG. 8 depict a top-down view an example of a multifocal lens 80 according to embodiments of the invention. Lens 80 includes region 81 having a first power and region 82 having a second power. Region 81 is located off center of the lens 80 to correlate with the center of the optical axis of the patient in which lens 80 is implanted. Similarly, region 82 may also be shifted to correspond to the optical axis of the patient.
  • The shift may also be an angular shift, in other words, the lens may be centered correctly, but may be tilted with respect to the optical axis of the patient. In such a case, the base power may be shifted and/or the multifocal power may be added after healing to compensate for the shift. FIG. 9 depict a side view an example of a multifocal lens 90 according to embodiments of the invention. Lens 90 includes region 91 having a first power and region 92 having a second power. Region 91 is tilted at angle φ 93 with respect to an optical axis of the lens (before adding the region 91 and/or adjusting region 92) to correspond to the optical axis of the patient in which the lens 90 is implant. The shift may also encompass both a lateral shift and/or a tilt. In which case a lens that includes aspects of FIGS. 8 and 9 would be preferable. Furthermore, a lens may include aspects of FIGS. 8 and/or 9, as well as FIG. 6A or FIG. 7A
  • Note that the size and power of the multifocal zones may be selected based on the pupil dilation of the patient in which the lens is implanted. In other words, placement and size of the near and distance vision portions may be selected based on the pupil dilation response. Thus, for a particular patient, the sizes and placement may be selected to allow for one or both of near and distance vision when the pupil is maximally dilated. The size and power may also be selected based on the habits of the patient. For example a person that holds reading material close to their face (or eyes) for reading may prefer a size and/or power that is different from a person that holds reading material farther from their face (or eyes). As another example, a person that does most of their reading from a computer screen may like to have a reading distance of 24 inches, while a person that mostly reads books or newspapers may like to have a reading distance of 12-18 inches.
  • The following is an example of a clinical scenario to illustrate creating a multifocal LAL according to embodiments of the invention. A cataract patient has a LAL implanted and after postoperative healing, manifest refraction indicates that the patient requires a −2.0 D change in the LAL power to obtain emmetropia. FIG. 10A illustrates the interference pattern 100 of the unirradiated LAL at its preirradiation best focus position along the optical axis of the interferometer. A common practice among cataract surgeons is to leave the patient slightly myopic in at least one eye so that only −1.4 D of power is initially removed from the LAL, which is shown the interference pattern 101 in FIG. 10B. The patient is then allowed a time period, e.g. few hours or days, to see how well this correction is tolerated. For purposes of this example, assume that the patient now desires to be brought to emmetropia. An additional dose of radiation will adjust the base power of the lens. FIG. 10C shows the interference pattern 102 of the LAL at the original preirradiation best focus position 24 hours after the second spherical irradiation correction. A comparison of FIGS. 10B and 10C shows an increase in the number of fringes of defocus, i.e. OPD, which corresponds to an additional −0.6 D of correction or −2.0 D of overall power change. After bringing the patient to emmetropia, the ophthalmologist can impart multifocality to the LAL by irradiating a third time. In this example, a 2 mm zone in the central part of the LAL (the Bull's Eye configuration) was irradiated to add back +2.0 D of power to the LAL. This is shown in FIG. 10D, which shows that a central part 104 of the LAL has been brought back to its initial refractive power. When finished adjusting the lens, the LAL may be irradiated for lock-in, which prevents ambient radiation from changing the LAL. Lock-in radiation consumes most of the remaining light reactive material in the LAL.
  • Note that in the above examples, the multifocal zone or zones has been spherical (e.g. 61 of FIG. 6B) or circular (e.g. 61 of FIG. 6A) in nature. However, noncircular and/or nonspherical zones may be used. For example, a multifocal zone may be aspherically shaped along an axis through the lens (e.g. vertically in the view of FIG. 6B). A lens may be elliptically shaped, cylindrically shaped, or rectangularly shaped along an axis across the lens (e.g. horizontally in the view of FIG. 6A).
  • Although the present invention and its advantages have been described in detail, it should be understood that various changes, substitutions and alterations can be made herein without departing from the spirit and scope of the invention as defined by the appended claims. Moreover, the scope of the present application is not intended to be limited to the particular embodiments of the process, machine, manufacture, composition of matter, means, methods and steps described in the specification. As one of ordinary skill in the art will readily appreciate from the disclosure of the present invention, processes, machines, manufacture, compositions of matter, means, methods, or steps, presently existing or later to be developed that perform substantially the same function or achieve substantially the same result as the corresponding embodiments described herein may be utilized according to the present invention. Accordingly, the appended claims are intended to include within their scope such processes, machines, manufacture, compositions of matter, means, methods, or steps.

Claims (8)

1. A multifocal lens comprising:
a first portion of the lens has a first focal length that provides distance vision; and
a second portion of the lens that includes a material that is optically reactive to an external stimulus and has a focal length that is adjusted to a second focal length by application of the stimulus and provides near vision;
wherein the second portion has a substantially circular shape and is located at a center of the lens, and the first portion has a substantially annulus shape and is located around the second portion.
2. A multifocal lens comprising:
a first portion of the lens has a first focal length that provides distance vision;
a second portion of the lens that includes a material that is optically reactive to an external stimulus and has a focal length that is adjusted to a second focal length by application of the stimulus and provides distance vision; and
a third portion of the lens that has the first focal length;
wherein the first portion has a substantially circular shape and is located at a center of the lens, and the second portion has a substantially annulus shape and is located around the first portion, and the third portion has a substantially annulus shape and is located around the second portion.
3. A multifocal lens comprising:
a first portion of the lens has a first focal length; and
a second portion of the lens that includes a material that is optically reactive to an external stimulus and has a focal length that is adjusted to a second focal length by application of the stimulus;
wherein the first focal length is different from the second focal length, and the second portion has a substantially circular shape and is located at non-central portion of the lens, and the first portion is located around the second portion.
4. A multifocal lens comprising:
a first portion of the lens has a first focal length that is located on a first side of the lens; and
a second portion of the lens that includes a material that is optically reactive to an external stimulus and has a focal length that is adjusted to a second focal length by application of the stimulus;
wherein the first focal length is different from the second focal length, and the second portion has an optical axis that is at an angle with respect to an optical axis of the second side of the lens.
5. A method for using a lens comprising:
preparing a lens having a modifying composition (MC) dispersed therein, wherein the modifying composition is capable of stimulus-induced polymerization;
implanting the lens in an animal;
exposing a portion of the lens to an external stimulus that causes changes in the optical properties that change a focal length of the portion of the lens to a first focal length to reduce an error caused by a healing response of the animal;
exposing another portion of the lens to an external stimulus that causes changes in the optical properties that change a focal length of the portion of the lens to a second focal length that is different from the first focal length.
6. The method of claim 5, further comprising:
selecting at least one of the first focal length and the second focal length based on a habit of the animal.
7. The method of claim 5, further comprising:
selecting a size of at least one of the portion and the another portion based on a habit of the animal.
8. The method of claim 5, further comprising:
selecting a size of at least one of the portion and the another portion based on a pupil dilation response of the animal.
US10/915,948 2001-12-28 2004-08-11 Light adjustable multifocal lenses Abandoned US20050099597A1 (en)

Priority Applications (3)

Application Number Priority Date Filing Date Title
US10/328,859 US20030151831A1 (en) 2001-12-28 2002-12-24 Light adjustable multifocal lenses
US49496903P true 2003-08-13 2003-08-13
US10/915,948 US20050099597A1 (en) 2002-12-24 2004-08-11 Light adjustable multifocal lenses

Applications Claiming Priority (7)

Application Number Priority Date Filing Date Title
US10/915,948 US20050099597A1 (en) 2002-12-24 2004-08-11 Light adjustable multifocal lenses
EP04781126A EP1663074A1 (en) 2003-08-13 2004-08-13 Light adjustable multifocal lenses
JP2006523411A JP2007503850A (en) 2003-08-13 2004-08-13 Light adjustable multifocal lenses
PCT/US2004/026386 WO2005016191A1 (en) 2003-08-13 2004-08-13 Light adjustable multifocal lenses
US11/083,794 US7281795B2 (en) 1999-01-12 2005-03-18 Light adjustable multifocal lenses
US11/871,574 US20080086207A1 (en) 1999-01-12 2007-10-12 Light Adjustable Multifocal Lenses
US12/628,344 US7988285B2 (en) 1999-01-12 2009-12-01 Light adjustable multifocal lenses

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US10/328,859 Continuation-In-Part US20030151831A1 (en) 2001-12-28 2002-12-24 Light adjustable multifocal lenses

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US11/083,794 Continuation-In-Part US7281795B2 (en) 1999-01-12 2005-03-18 Light adjustable multifocal lenses

Publications (1)

Publication Number Publication Date
US20050099597A1 true US20050099597A1 (en) 2005-05-12

Family

ID=34198018

Family Applications (1)

Application Number Title Priority Date Filing Date
US10/915,948 Abandoned US20050099597A1 (en) 2001-12-28 2004-08-11 Light adjustable multifocal lenses

Country Status (4)

Country Link
US (1) US20050099597A1 (en)
EP (1) EP1663074A1 (en)
JP (1) JP2007503850A (en)
WO (1) WO2005016191A1 (en)

Cited By (41)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20050041203A1 (en) * 2003-08-20 2005-02-24 Lindacher Joseph Michael Ophthalmic lens with optimal power profile
US20050113911A1 (en) * 2002-10-17 2005-05-26 Peyman Gholam A. Adjustable intraocular lens for insertion into the capsular bag
US20050182489A1 (en) * 2001-04-27 2005-08-18 Peyman Gholam A. Intraocular lens adapted for adjustment via laser after implantation
US20050283109A1 (en) * 2003-03-07 2005-12-22 Peyman Gholam A Method and apparatus for lacrimal canal obstruction
US20060084949A1 (en) * 2000-03-21 2006-04-20 Peyman Gholam A Method and apparatus for accommodating intraocular lens
US20060082729A1 (en) * 2004-09-30 2006-04-20 The Hong Kong Polytechnic Univeristy Method of optical treatment
US20060216329A1 (en) * 2000-03-21 2006-09-28 Peyman Gholam A Drug delivery system and method
WO2007019389A1 (en) * 2005-08-05 2007-02-15 Visiogen, Inc. Accommodating diffractive intraocular lens
WO2007033831A1 (en) * 2005-09-23 2007-03-29 Schmidt Intraocularlinsen Gmbh Intraocular lens
US20070100443A1 (en) * 2005-10-27 2007-05-03 Peyman Gholam A Intraocular lens adapted for accommodation via electrical signals
US20070260157A1 (en) * 2004-11-12 2007-11-08 Sverker Norrby Devices and methods of selecting intraocular lenses
EP1882463A1 (en) * 2006-07-26 2008-01-30 Calhoun Vision Inc. A light adjustable lens (LAL) allowing an improved retinal safety
US20080062380A1 (en) * 2004-07-01 2008-03-13 Auckland Uniservices Limited Contact Lens and Method for Prevention of Myopia Progression
US20080103592A1 (en) * 2006-10-30 2008-05-01 Calhoun Vision, Inc. Piggyback lenses
US20080218687A1 (en) * 2007-03-09 2008-09-11 Auckland Uniservices Limited. Contact lens and method
US20080269889A1 (en) * 2007-04-30 2008-10-30 Simpson Michael J Haptic Junction Designs to Reduce Negative Dysphotopsia
US20090118828A1 (en) * 2007-11-06 2009-05-07 Altmann Griffith E Light-adjustable multi-element ophthalmic lens
US20090228101A1 (en) * 2007-07-05 2009-09-10 Visiogen, Inc. Intraocular lens with post-implantation adjustment capabilities
US8579970B1 (en) 2005-06-27 2013-11-12 Visiogen, Inc. Magnifying intraocular lens
US8752958B2 (en) 1999-03-01 2014-06-17 Boston Innovative Optics, Inc. System and method for increasing the depth of focus of the human eye
WO2015038623A1 (en) * 2013-09-12 2015-03-19 Battelle Memorial Institute Lens modification methods
US9011532B2 (en) 2009-06-26 2015-04-21 Abbott Medical Optics Inc. Accommodating intraocular lenses
US9039760B2 (en) 2006-12-29 2015-05-26 Abbott Medical Optics Inc. Pre-stressed haptic for accommodating intraocular lens
US9198752B2 (en) 2003-12-15 2015-12-01 Abbott Medical Optics Inc. Intraocular lens implant having posterior bendable optic
US9204962B2 (en) 2013-03-13 2015-12-08 Acufocus, Inc. In situ adjustable optical mask
US9271830B2 (en) 2002-12-05 2016-03-01 Abbott Medical Optics Inc. Accommodating intraocular lens and method of manufacture thereof
US9427922B2 (en) 2013-03-14 2016-08-30 Acufocus, Inc. Process for manufacturing an intraocular lens with an embedded mask
US9504560B2 (en) 2002-01-14 2016-11-29 Abbott Medical Optics Inc. Accommodating intraocular lens with outer support structure
US9545303B2 (en) 2011-12-02 2017-01-17 Acufocus, Inc. Ocular mask having selective spectral transmission
US9603703B2 (en) 2009-08-03 2017-03-28 Abbott Medical Optics Inc. Intraocular lens and methods for providing accommodative vision
US9636213B2 (en) 2005-09-30 2017-05-02 Abbott Medical Optics Inc. Deformable intraocular lenses and lens systems
US9681800B2 (en) 2005-10-27 2017-06-20 The Arizona Board Of Regents On Behalf Of The University Of Arizona Holographic adaptive see-through phoropter
US9814570B2 (en) 1999-04-30 2017-11-14 Abbott Medical Optics Inc. Ophthalmic lens combinations
US9968441B2 (en) 2008-03-28 2018-05-15 Johnson & Johnson Surgical Vision, Inc. Intraocular lens having a haptic that includes a cap
US9987125B2 (en) 2012-05-02 2018-06-05 Johnson & Johnson Surgical Vision, Inc. Intraocular lens with shape changing capability to provide enhanced accomodation and visual acuity
US9993336B2 (en) 2016-06-06 2018-06-12 Omega Ophthalmics Llc Prosthetic capsular devices, systems, and methods
US10004594B2 (en) 2014-06-19 2018-06-26 Omega Ophthalmics Llc Prosthetic capsular devices, systems, and methods
US10111746B2 (en) 2016-10-21 2018-10-30 Omega Ophthalmics Llc Prosthetic capsular devices, systems, and methods
US10136989B2 (en) 2012-02-22 2018-11-27 Omega Ophthalmics Llc Prosthetic implant devices
US10254562B2 (en) * 2008-04-04 2019-04-09 Battelle Memorial Institute Methods for tailoring the refractive index of lenses
US10271945B2 (en) 2018-05-08 2019-04-30 Omega Ophthalmics Llc Prosthetic capsular devices, systems, and methods

Families Citing this family (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7281795B2 (en) 1999-01-12 2007-10-16 Calhoun Vision, Inc. Light adjustable multifocal lenses
CA2754775C (en) * 2009-03-04 2016-09-27 Aaren Scientific Inc. System for characterizing a cornea and obtaining an ophthalmic lens
CN102436075B (en) * 2011-12-23 2013-04-10 苏州大学 Progressive addition lens with large visual areas and low astigmatism

Citations (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4260725A (en) * 1979-12-10 1981-04-07 Bausch & Lomb Incorporated Hydrophilic contact lens made from polysiloxanes which are thermally bonded to polymerizable groups and which contain hydrophilic sidechains
US4608050A (en) * 1983-07-21 1986-08-26 Innovative Surgical Products, Inc. Correction of defects in the eye and compositions therefor
US5066301A (en) * 1990-10-09 1991-11-19 Wiley Robert G Variable focus lens
US5225858A (en) * 1987-06-01 1993-07-06 Valdemar Portney Multifocal ophthalmic lens
US5236970A (en) * 1987-02-05 1993-08-17 Allergan, Inc. Optically clear reinforced silicone elastomers of high optical refractive index and improved mechanical properties for use in intraocular lenses
US5278258A (en) * 1992-05-18 1994-01-11 Allergan, Inc. Cross-linked silicone polymers, fast curing silicone precursor compositions, and injectable intraocular lenses
US5444106A (en) * 1992-04-21 1995-08-22 Kabi Pharmacia Ophthalmics, Inc. High refractive index silicone compositions
US5443506A (en) * 1992-11-18 1995-08-22 Garabet; Antoine L. Lens with variable optical properties
US5549668A (en) * 1992-09-24 1996-08-27 O'donnell, Jr.; Francis E. In vivo modification of refractive power of an intraocular lens implant
US5712721A (en) * 1993-04-07 1998-01-27 Technology Partnership, Plc Switchable lens
US5728155A (en) * 1996-01-22 1998-03-17 Quantum Solutions, Inc. Adjustable intraocular lens
US6450642B1 (en) * 1999-01-12 2002-09-17 California Institute Of Technology Lenses capable of post-fabrication power modification
US6491391B1 (en) * 1999-07-02 2002-12-10 E-Vision Llc System, apparatus, and method for reducing birefringence
US20030003295A1 (en) * 2000-11-27 2003-01-02 Dreher Andreas W. Apparatus and method of correcting higher-order aberrations of the human eye
US20030081172A1 (en) * 2001-10-25 2003-05-01 Dreher Andreas W. Eyeglass manufacturing method using variable index layer

Family Cites Families (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20030151831A1 (en) * 2001-12-28 2003-08-14 Sandstedt Christian A. Light adjustable multifocal lenses

Patent Citations (16)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4260725A (en) * 1979-12-10 1981-04-07 Bausch & Lomb Incorporated Hydrophilic contact lens made from polysiloxanes which are thermally bonded to polymerizable groups and which contain hydrophilic sidechains
US4608050A (en) * 1983-07-21 1986-08-26 Innovative Surgical Products, Inc. Correction of defects in the eye and compositions therefor
US5376694A (en) * 1987-02-05 1994-12-27 Allergan, Inc. Optically clear reinforced silicone elastomers of high optical refractive index and improved mechanical properties for use in intraocular lenses
US5236970A (en) * 1987-02-05 1993-08-17 Allergan, Inc. Optically clear reinforced silicone elastomers of high optical refractive index and improved mechanical properties for use in intraocular lenses
US5225858A (en) * 1987-06-01 1993-07-06 Valdemar Portney Multifocal ophthalmic lens
US5066301A (en) * 1990-10-09 1991-11-19 Wiley Robert G Variable focus lens
US5444106A (en) * 1992-04-21 1995-08-22 Kabi Pharmacia Ophthalmics, Inc. High refractive index silicone compositions
US5278258A (en) * 1992-05-18 1994-01-11 Allergan, Inc. Cross-linked silicone polymers, fast curing silicone precursor compositions, and injectable intraocular lenses
US5549668A (en) * 1992-09-24 1996-08-27 O'donnell, Jr.; Francis E. In vivo modification of refractive power of an intraocular lens implant
US5443506A (en) * 1992-11-18 1995-08-22 Garabet; Antoine L. Lens with variable optical properties
US5712721A (en) * 1993-04-07 1998-01-27 Technology Partnership, Plc Switchable lens
US5728155A (en) * 1996-01-22 1998-03-17 Quantum Solutions, Inc. Adjustable intraocular lens
US6450642B1 (en) * 1999-01-12 2002-09-17 California Institute Of Technology Lenses capable of post-fabrication power modification
US6491391B1 (en) * 1999-07-02 2002-12-10 E-Vision Llc System, apparatus, and method for reducing birefringence
US20030003295A1 (en) * 2000-11-27 2003-01-02 Dreher Andreas W. Apparatus and method of correcting higher-order aberrations of the human eye
US20030081172A1 (en) * 2001-10-25 2003-05-01 Dreher Andreas W. Eyeglass manufacturing method using variable index layer

Cited By (64)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8752958B2 (en) 1999-03-01 2014-06-17 Boston Innovative Optics, Inc. System and method for increasing the depth of focus of the human eye
US9814570B2 (en) 1999-04-30 2017-11-14 Abbott Medical Optics Inc. Ophthalmic lens combinations
US20060084949A1 (en) * 2000-03-21 2006-04-20 Peyman Gholam A Method and apparatus for accommodating intraocular lens
US20060216329A1 (en) * 2000-03-21 2006-09-28 Peyman Gholam A Drug delivery system and method
US8162927B2 (en) 2000-03-21 2012-04-24 Gholam A. Peyman Method and apparatus for accommodating intraocular lens
US20050182489A1 (en) * 2001-04-27 2005-08-18 Peyman Gholam A. Intraocular lens adapted for adjustment via laser after implantation
US9504560B2 (en) 2002-01-14 2016-11-29 Abbott Medical Optics Inc. Accommodating intraocular lens with outer support structure
US20050113911A1 (en) * 2002-10-17 2005-05-26 Peyman Gholam A. Adjustable intraocular lens for insertion into the capsular bag
US9271830B2 (en) 2002-12-05 2016-03-01 Abbott Medical Optics Inc. Accommodating intraocular lens and method of manufacture thereof
US10206773B2 (en) 2002-12-05 2019-02-19 Johnson & Johnson Surgical Vision, Inc. Accommodating intraocular lens and method of manufacture thereof
US20050283109A1 (en) * 2003-03-07 2005-12-22 Peyman Gholam A Method and apparatus for lacrimal canal obstruction
US20050041203A1 (en) * 2003-08-20 2005-02-24 Lindacher Joseph Michael Ophthalmic lens with optimal power profile
US7192138B2 (en) * 2003-08-20 2007-03-20 Novartis Ag Ophthalmic lens with optimal power profile
US20060215109A1 (en) * 2003-08-20 2006-09-28 Lindacher Joseph M Ophthalmic lens with optimal power profile
US9198752B2 (en) 2003-12-15 2015-12-01 Abbott Medical Optics Inc. Intraocular lens implant having posterior bendable optic
US7766478B2 (en) 2004-07-01 2010-08-03 Auckland Uniservices Limited Contact lens and method for prevention of myopia progression
US7997725B2 (en) 2004-07-01 2011-08-16 Auckland Uniservices Limited Contact lens and method for prevention of myopia progression
US20110001923A1 (en) * 2004-07-01 2011-01-06 Auckland Uniservices Limited Contact lens and method for prevention of myopia progression
US20080062380A1 (en) * 2004-07-01 2008-03-13 Auckland Uniservices Limited Contact Lens and Method for Prevention of Myopia Progression
USRE47006E1 (en) * 2004-09-30 2018-08-28 The Hong Kong Polytechnic University Lens for optical treatment
US7506983B2 (en) * 2004-09-30 2009-03-24 The Hong Kong Polytechnic University Method of optical treatment
US20060082729A1 (en) * 2004-09-30 2006-04-20 The Hong Kong Polytechnic Univeristy Method of optical treatment
USRE43851E1 (en) 2004-09-30 2012-12-11 The Hong Kong Polytechnic University Method of optical treatment
USRE45147E1 (en) * 2004-09-30 2014-09-23 The Hong Kong Polytechnic University Lens for optical treatment
US8087782B2 (en) * 2004-11-12 2012-01-03 Amo Groningen B.V. Devices and methods of selecting intraocular lenses
US20070260157A1 (en) * 2004-11-12 2007-11-08 Sverker Norrby Devices and methods of selecting intraocular lenses
US8540370B2 (en) 2004-11-12 2013-09-24 Amo Groningen Bv Devices and methods for selecting intraocular lenses
US8579970B1 (en) 2005-06-27 2013-11-12 Visiogen, Inc. Magnifying intraocular lens
US20070031473A1 (en) * 2005-08-05 2007-02-08 Peyman Gholam A Drug delivery system and method
WO2007019389A1 (en) * 2005-08-05 2007-02-15 Visiogen, Inc. Accommodating diffractive intraocular lens
WO2007033831A1 (en) * 2005-09-23 2007-03-29 Schmidt Intraocularlinsen Gmbh Intraocular lens
US8109999B2 (en) 2005-09-23 2012-02-07 Norbert Hampp Intraocular lens
US20090157178A1 (en) * 2005-09-23 2009-06-18 Norbert Hampp Intraocular lens
US9636213B2 (en) 2005-09-30 2017-05-02 Abbott Medical Optics Inc. Deformable intraocular lenses and lens systems
US9681800B2 (en) 2005-10-27 2017-06-20 The Arizona Board Of Regents On Behalf Of The University Of Arizona Holographic adaptive see-through phoropter
US20070142909A1 (en) * 2005-10-27 2007-06-21 Minu Llc External lens adapted to change refractive properties
US20070100443A1 (en) * 2005-10-27 2007-05-03 Peyman Gholam A Intraocular lens adapted for accommodation via electrical signals
US7993399B2 (en) 2005-10-27 2011-08-09 Gholam A. Peyman External lens adapted to change refractive properties
EP1882463A1 (en) * 2006-07-26 2008-01-30 Calhoun Vision Inc. A light adjustable lens (LAL) allowing an improved retinal safety
US20080103592A1 (en) * 2006-10-30 2008-05-01 Calhoun Vision, Inc. Piggyback lenses
US9039760B2 (en) 2006-12-29 2015-05-26 Abbott Medical Optics Inc. Pre-stressed haptic for accommodating intraocular lens
US20080218687A1 (en) * 2007-03-09 2008-09-11 Auckland Uniservices Limited. Contact lens and method
US7832859B2 (en) 2007-03-09 2010-11-16 Auckland Uniservices Limited Contact lens and method
US20080269889A1 (en) * 2007-04-30 2008-10-30 Simpson Michael J Haptic Junction Designs to Reduce Negative Dysphotopsia
US20090228101A1 (en) * 2007-07-05 2009-09-10 Visiogen, Inc. Intraocular lens with post-implantation adjustment capabilities
US9421089B2 (en) 2007-07-05 2016-08-23 Visiogen, Inc. Intraocular lens with post-implantation adjustment capabilities
US20090118828A1 (en) * 2007-11-06 2009-05-07 Altmann Griffith E Light-adjustable multi-element ophthalmic lens
US9968441B2 (en) 2008-03-28 2018-05-15 Johnson & Johnson Surgical Vision, Inc. Intraocular lens having a haptic that includes a cap
US10254562B2 (en) * 2008-04-04 2019-04-09 Battelle Memorial Institute Methods for tailoring the refractive index of lenses
US9011532B2 (en) 2009-06-26 2015-04-21 Abbott Medical Optics Inc. Accommodating intraocular lenses
US10052194B2 (en) 2009-06-26 2018-08-21 Johnson & Johnson Surgical Vision, Inc. Accommodating intraocular lenses
US9603703B2 (en) 2009-08-03 2017-03-28 Abbott Medical Optics Inc. Intraocular lens and methods for providing accommodative vision
US10105215B2 (en) 2009-08-03 2018-10-23 Johnson & Johnson Surgical Vision, Inc. Intraocular lens and methods for providing accommodative vision
US9545303B2 (en) 2011-12-02 2017-01-17 Acufocus, Inc. Ocular mask having selective spectral transmission
US10136989B2 (en) 2012-02-22 2018-11-27 Omega Ophthalmics Llc Prosthetic implant devices
US9987125B2 (en) 2012-05-02 2018-06-05 Johnson & Johnson Surgical Vision, Inc. Intraocular lens with shape changing capability to provide enhanced accomodation and visual acuity
US9603704B2 (en) 2013-03-13 2017-03-28 Acufocus, Inc. In situ adjustable optical mask
US9204962B2 (en) 2013-03-13 2015-12-08 Acufocus, Inc. In situ adjustable optical mask
US9427922B2 (en) 2013-03-14 2016-08-30 Acufocus, Inc. Process for manufacturing an intraocular lens with an embedded mask
WO2015038623A1 (en) * 2013-09-12 2015-03-19 Battelle Memorial Institute Lens modification methods
US10004594B2 (en) 2014-06-19 2018-06-26 Omega Ophthalmics Llc Prosthetic capsular devices, systems, and methods
US9993336B2 (en) 2016-06-06 2018-06-12 Omega Ophthalmics Llc Prosthetic capsular devices, systems, and methods
US10111746B2 (en) 2016-10-21 2018-10-30 Omega Ophthalmics Llc Prosthetic capsular devices, systems, and methods
US10271945B2 (en) 2018-05-08 2019-04-30 Omega Ophthalmics Llc Prosthetic capsular devices, systems, and methods

Also Published As

Publication number Publication date
JP2007503850A (en) 2007-03-01
WO2005016191A1 (en) 2005-02-24
EP1663074A1 (en) 2006-06-07

Similar Documents

Publication Publication Date Title
US8906089B2 (en) Multifocal ophthalmic lens
Piers et al. Theoretical comparison of aberration-correcting customized and aspheric intraocular lenses
US10085833B2 (en) Multifocal ophthalmic lens
US9814570B2 (en) Ophthalmic lens combinations
JP3677240B2 (en) Application of wavefront sensor to capable magnification adjusted after manufacture lenses
US7717558B2 (en) Pseudo-accommodative IOL having diffractive zones with varying areas
AU2006297533B2 (en) Deformable intraocular lenses and lens systems
CN1217632C (en) Intraocular lens system
Holladay et al. A new intraocular lens design to reduce spherical aberration of pseudophakic eyes
JP4486122B2 (en) Two optical elements which form a lens with variable optical power of the combination for use as an intraocular lens
US6923539B2 (en) Aspheric lenses
RU2377963C2 (en) Aspheric intraocular lens for higher contrast
US6966649B2 (en) Adaptive optic lens system and method of use
CN1306918C (en) Lenses capable of post-fabrication power modification
US8535376B2 (en) Aspheric lenses and lens family
KR101489170B1 (en) Ophthalmic lenses for prevention of myopia progression
CA2430865C (en) Durable flexible attachment components for accommodating intraocular lens
US8235525B2 (en) Method for making an aspheric intraocular lens
US20060116764A1 (en) Apodized aspheric diffractive lenses
EP2365379B1 (en) Method of forming an ophthalmic lens for extending the depth of focus of an eye
US20070129798A1 (en) Intraocular device
US8715346B2 (en) Intraocular, accommodating lens and methods of use
EP1982229B1 (en) Pseudo-accomodative iol having diffractive zones with varying areas
US20050203619A1 (en) Aspheric lenses and lens family
US6860601B2 (en) Adaptive optic lens system and method of use

Legal Events

Date Code Title Description
AS Assignment

Owner name: CALHOUN VISION, CALIFORNIA

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:SANDSTEDT, CHRISTIAN A.;JETHMALANI, JAGDISH M.;CHANG, SHIAO H.;REEL/FRAME:016148/0370;SIGNING DATES FROM 20041201 TO 20050105